EP0220629B1

EP0220629B1 - Radiation image recording and read-out apparatus

Info

Publication number: EP0220629B1
Application number: EP86114429A
Authority: EP
Inventors: Kazuo Fuji Photo Film Co. Ltd. Shimura; Nobufumi Fuji Photo Film Co. Ltd. Mori; Shigeru Fuji Photo Film Co. Ltd. Saotome; Ryoichi Fuji Photo Film Co. Ltd. Yoshimura; Hideo Fuji Photo Film Co. Ltd. Watanabe; Yuichi Fuji Photo Film Co. Ltd. Hosoi
Original assignee: Fuji Photo Film Co Ltd
Current assignee: Fujifilm Holdings Corp
Priority date: 1985-10-18
Filing date: 1986-10-17
Publication date: 1990-07-11
Anticipated expiration: 2006-10-17
Also published as: EP0220629A2; DE3688511D1; DE3688511T2; EP0220629A3; US4835386A; DE3672561D1; DE3650017D1; DE3650489T2; DE3650017T2; DE3650489D1

Description

Field of the invention

This invention relates to a radiation image recording and read-out apparatus for exposing a stimulable phosphor sheet to a radiation passing through an object to have a radiation image of the object stored thereon, exposing the stimulable phosphor sheet to stimulating rays which cause it to emit light in proportion to the stored radiation energy, and detecting the emitted light and converting it into an electric signal. This invention particularly relates to a radiation image recording and read-out apparatus in which the stimulable phosphor sheet is used repeatedly. This invention also relates to a radiation image storage panel for use in the radiation image recording and read-out apparutus, and a method of moving the radiation image storage panel.

Description of the prior art

When certain kinds of phosphors are exposed to a radiation such as X-rays, a-rays, P-rays, y-rays, cathode rays or ultraviolet rays, they store a part of the energy of the radiation. Then, when the phosphor which has been exposed to the radiation is exposed to stimulating rays such as visible light, light is emitted by the phosphor in proportion to the stored energy of the radiation. A phosphor exhibiting such properties is referred to as a stimulable phosphor.
As disclosed in U.S. Patent No. 4,258,264, 4,276,473, 4,315,318 and 4,387,428, and Japanese Unexamined Patent Publication No. 56(1918)-11395, it has been proposed to use a stimulable phosphor in a radiation image recording and reproducing system. Specifically, a sheet comprising the stimulable phosphor (hereinafter referred to as a stimulable phosphor sheet or simply as a sheet) is first exposed to a radiation passing through an object to have a radiation image stored thereon, and is then scanned with stimulating rays which cause it to emit light in proportion to the stored radiation energy. The light emitted by the stimulable phosphor sheet when the sheet is exposed to the stimulating rays is photoelectrically detected and converted into an electric image signal, which is processed as desired to reproduce a visible image having an improved image quality, particularly a high diagnostic efficiency and accuracy. The finally obtained visible image may be reproduced in the form of a hard copy or may be displayed on a cathode ray tube (CRT). In this radiation image recording and reproducing system, the stimulable phosphor sheet is used to temporarily store the radiation image in order to reproduce the final visible image therefrom on a final recording medium. For economical reasons, therefore, it is desirable that the stimulable phosphor sheet be used repeatedly.
Further, in a mobile X-ray diagnostic station such as a travelling X-ray diagnostic station in the form of a vehicle like a bus which is provided with a radiation image recording and read-out apparatus for use in the aforesaid radiation image recording and reproducing system and moves from place to place to record radiation images for mass medical examinations, it is disadvantageous to load the mobile X-ray diagnostic station with a large number of stimulable phosphor sheets, and the number of the stimulable phosphor sheets which can be loaded on the mobile X-ray diagnostic station is limited. Therefore, it is desired to load the mobile X-ray diagnostic station with stimulable phosphor sheets which can be used repeatedly, store the radiation images of the respective objects on the stimulable phosphor sheets, transfer the electric image signals read out from the stimulable phosphor sheets to a recording medium having a large storage capacity, such as a magnetic tape, and ciruclate and reuse the stimulable phosphor sheets for further image recording and read-out operations, thereby to obtain the radiation image signals of many objects. Further, when image recording is conducted continuously by circulating and reusing the stimulable phosphor sheets, it becomes possible to increase the image recording speed in mass medical examinations. This is very advantageous in practical use.
In order to reuse stimulable phosphor sheets as described above, the radiation energy remaining on the stimulable phosphor sheet after it is scanned with stimulating rays to read out the radiation image stored thereon should be erased by exposure to light or heat as described, for example, in U.S. Patent No. 4,400,619 or Japanese Unexamined Patent Publication No. 56(1981)-12599. The stimulable phosphor sheet should then be used again for radiation image recording.
From the aforesaid viewpoint, the applicant proposed in EP-A-0 125 800 an apparatus of the type defined in the pre-characterizing part of claim 1:
In the prior art apparatus said stimulable phosphor sheet is circulated through the image recording section, the image read-out section and the erasing section and reused for radiation image recording.
In the aforesaid radiation image recording and read-out apparatus, recording and read-out of radiation images can be conducted continuously and efficiently.
However, the aforesaid radiation image recording and read-out apparatus has the drawback that, since the circulation path for the stimulable phosphor sheet is provided in the apparatus, the apparatus becomes large.
The primary problem to be solved by the present invention is to provide a radiation image recording and read-out apparatus which is very small and in which a stimulable phosphor sheet is used repeatedly.
This problem is solved by the characterizing features of claim 1.
The apparatus according to the invention is small and provided with a single mechanism for feeding a stimulable phosphor sheet and in which the stimulable phosphor sheet is used repeatedly and image recording is conducted continuously.
The apparatus is free from a deviation in position of the stimulable phosphor sheet in the course of conducting image recording, image read-out and erasing, threeby providing a radiation image having an improved image quality, particularly a high diagnostic efficiency and accuracy.
In the radiation image recording and read-out apparatus in accordance with the present invention, when the radiation image stored on the stimulable phosphor sheet is read out at the image read-out section provided with the sub-scanning means and the main scanning means, the stimulable phosphor sheet is moved from the light shielding cover projected out of the case into the case. Or, in the case where image read-out is conducted after returning the stimulable phosphor sheet, the stimulable phosphor sheet is moved for image read-out from the case into the light shielding cover projected out of the case. Thus the sheet movement space for the sub-scanning is ensured by projecting the light shielding cover out of the case. Therefore, it is only necessary that the size of the case be such that the light shielding cover and the stimulable phosphor sheet can be housed therein when the apparatus is not used, and it is possible to make the case small, approximately to a size for housing a single stimulable phosphor sheet.

Brief description of the drawings

Figure 1 is a general perspective view showing an embodiment of the radiation image recording and read-out apparatus in accordance with the present invention;
Figure 2 is a perspective view showing the principal parts of the embodiment of Figure 1,
Figures 3 and 4 are sectional side views showing the conditions of the embodiment of Figure 1 during image recording and image read-out,
Figures 5 to 10 are sectional side views showing a part of further embodiments of the radiation image recording and read-out apparatus in accordance with the present invention,
Figures 11 and 12 are a plan view and a side view showing an example of the stimulating ray reflection optical system used in the radiation image recording and read-out apparatus of the present invention,
Figure 13 is a side view showing another example of the stimulating ray reflection optical system used in the radiation image recording and read-out apparatus of the present invention,
Figures 14, 15 and 16 are perspective views showing further embodiments of the radiation image recording and read-out apparatus in accordance with the present invention,
Figure 17A is a perspective view showing the long photomultiplier used in the radiation image recording and read-out apparatus of the present invention,
Figure 17B is a sectional view taken along the 1-1 of Figure 17A, and
Figure 18 is a circuit diagram showing the drive circuit of the photomultiplier shown in Figure 17A.

Description of the preferred embodiments

The present invention will hereinbelow be described in further detail with reference to the accompanying drawings.
Referring to Figure 1, an embodiment of the radiation image recording and read-out apparatus in accordance with the present invention comprises a main body 20 housed in a wall 10 of a medical examination room of a hospital or the like, and a radiation source housing section 30 adapted for housing in the wall 10. The main body 20 is constituted by a case 25 housing a light shielding cover 26 projectable out of the case 25. When the apparatus is not in use, the light shielding cover 26 is housed in the case 25, i.e. in the wall 10, and the radiation source housing section 30 is housed in a recess 12 in the wall 10. When the apparatus is to be used, the light shielding cover 26 and the radiation source housing section 30 are pulled out of the wall 10 by means of, for example, handles 21 and 31 respectively.
Figure 2 shows the configuration of the main body 20 in detail, and Figure 3 is a sectional side view showing the configuration of the main body 20 and the radiation source housing section 30. A stimulable phosphor sheet 22 comprising a platelike substrate 22A and a stimulable phosphor layer 22B overlaid on the substrate 22A is disposed inside of the case 25 of the main body 25. The substrate 22A of the stimulable phosphor sheet 22 is formed to be larger than the stimulable phosphor layer 22B, and the portions of the substrate 22A around the stimulable phosphor layer 22B constitute holding portions 22a, 22b, 22c and 22d. In this embodiment, the stimulable phosphor sheet 22 is positioned so that the stimulable phosphor layer 22B comes under the substrate 22A. The holding portions 22b and 22d are slideably supported on rails 23, 23, and the stimulable phosphor sheet 22 is thereby supported inside of the case 25. The length and width of the case 25 are adjusted to be slightly greater than those of the stimulable phosphor sheet 22.
As shown in Figure 3, the case 25 is provided with an opening 25a at an end portion on the side of the wall 10, and the light shielding cover 26 housed in the case 25 is projectable out of the case 25 through the opening 25a. Though the light shielding cover 26 manually projected out of the case 25 by means of the handle 21 in this embodiment, the light shielding cover 26 may also be moved by a drive device to project it out of the case 25. The light shielding cover 26 is provided with a sheet passage opening 26a at one end portion, i.e. at the end portion on the side supported by the case 25 when the light shielding cover 26 is projected out of the case 25. Therefore, the inside of the light shielding cover 26 is communicated with the inside of the case 25 via the sheet passage opening 26a. When the light shielding cover 26 is housed in the case 25, the stimulable phosphor sheet 22 is positioned inside of the light shielding cover 26.
The upper surface of the light shielding cover 26, i.e. the surface facing the stimulable phosphor sheet 22 from above when the stimulable phosphor sheet 22 is housed in the light shielding cover 26, constitutes an image recording table 32. The radiation source housing section 30 houses a radiation source 33 which may be an X-ray tube or the like and which faces the image recording table 32 as shown in Figure 3 when the radiation source housing section 30 and the light shielding cover 26 are pulled out from the wall 10 in the course of using the apparatus. The case 25 and the portions of the light shielding cover 26 outside of the image recording table 32 are lined with a radiation absorbing material such as a lead plate so that no fogging is produced on the stimulable phosphor sheet 22 by environmental or other such radiations other than the radiation used for image recording.
When a radiation image of an object 34 should be recorded, the object 34 is made to lie, for example, on his back, on the image recording table 32 of the light shielding cover 26 projected out of the wall 10, and the stimulable phosphor sheet 22 is conveyed by drive rollers 58, 58 as described later up to the exposure position facing the image recording table 32 as shown in Figure 3. The radiation source 33 is activated in this condition, and the stimulable phosphor sheet 22 is exposed to a radiation 35 passing through the object 34 to have a radiation image of the object 34 stored thereon, specifically on the stimulable phosphor layer 22B formed on the lower surface side of the stimulable phosphor sheet 22. The stimulable phosphor sheet 22 is supported inside of the light shielding cover 26 by rails 27, 27 which are approximately aligned with the rails 23, 23 of the case 25. Thus in this embodiment, an image recording section 40 is constituted by the image recording table 32 and the radiation source 33. Also, as shown in Figure 1, the legs of the object 34 are supported by a supporting base 15 adapted to be housed in the wall 10.
An image read-out section 50 is provided at a lower section inside of the case 25. The image read-out section 50 is provided with a laser beam source 51, a mirror 53 for reflecting a laser beam 52 emitted as stimulating rays by the laser beam source 51, a beam expander 54 for adjusting the beam diameter of the laser beam 52 to a predetermined value, a cylindrical lens 55 for making the laser beam 52 impinge upon a mirror surface of a light deflector 56 described later so as to form a linear image normal to the rotation axis of the light deflector 56, and the light deflector 56 constituted by a multi-face rotating mirror or the like for reflecting and deflecting the laser beam 52. The image read-out section 50 is also provided with a long mirror 57 for reflecting the deflected laser beam 52 so that the laser beam 52 scans the stimulable phosphor sheet 22, specifically the stimulable phosphor layer 22B, in one direction, and drive rollers 58, 58 acting as a sub-scanning means constituted by a pair of nip rollers for grasping the stimulable phosphor sheet 22 and rotated at a predetermined speed. The image read-out section 50 also comprises a long photomultiplier 59 acting as a photoelectric read-out means and positioned so that the light receiving face extends along the scanning line (main scanning line) of the laser beam 52 on the stimulable phosphor sheet 22, and a long light guide reflection mirror 60 positioned along the long photomultiplier 59. Also, an f8 lens 61 and a cylindrical lens 62 are positioned between the light deflector 56 and the mirror 57, and the laser beam 52 is thereby made to converge to a predetermined beam diameter at every position on the stimulable phosphor sheet 22.
As shown in Figure 4, after the radiation image of the object 34 is stored on the stimulable phosphor sheet 22 as mentioned above, the drive rollers 58, 58 are rotated and the stimulable phosphor sheet 22 is moved at a predetermined speed from the light shielding cover 26 to the case 25. When radiation image recording is conducted, the drive rollers 58, 58 grasp the holding portion 22a at one end of the stimulable phosphor sheet 22. Therefore, when the drive rollers 58, 58 are rotated after image recording is conducted, the stimulable phosphor sheet 22 can be immediately conveyed as mentioned above. Simultaneously with the conveyance of the stimulable phosphor sheet 22, the laser beam source 51 and the light deflector 56 are activated, and the laser beam 52 is made to scan on the sheet 22. As the stimulable phosphor sheet 22 is exposed to the laser beam 52, the exposed portion of the sheet 22 emits light 63 carrying the radiation image stored on the sheet 22. The emitted light 63 is efficiently detected by the long photomultiplier 59 directly or after being reflected by the light guide reflection mirror 60. The scanning of the laser beam 52 in the main scanning direction is conducted as described above, and at the same time the stimulable phosphor sheet 22 is moved in the sub-scanning direction as mentioned above. Accordingly, the emitted light 63, i.e. the radiation image, is two-dimensionally read out of the stimulable phosphor sheet 22. The read-out image signal generated by the long photomultiplier 59 is amplified, digitized and processed by a read-out circuit 64, and then sent to an image reproducing apparatus (not shown) wherein the image signal is used for reproducing a visible radiation image. The image reproducing apparatus may be a display means such as a cathode ray tube (CRT) or an apparatus for light beam scanning recording on a light-sensitive film, or may be replaced by an apparatus for storing the image signal on an image file such as an optical disk or a magnetic disk. Also, the image signal may be sent to a remote position, where there are personnel and instruments for medical examination, through radio communication and used for radiation image reproduction and diagnosis.
As shown in Figure 4, when the stimulable phosphor sheet 22 is moved by the drive rollers 58, 58 in the sub-scanning direction, the sheet 22 passes through the sheet passage opening 26a and moves from the light shielding cover 26 to the case 25. The laser beam 52 scans the sheet 22 at the position near the opening 25a of the case 25. When image read-out is finished, the stimulable phosphor sheet 22 is positioned inside of the case 25. Therefore, it is not necessary to provide the case 25 with a special space for sub-scanning of the sheet 22, it only being necessary that the case 25 is of a size that is slightly larger than the sheet 22.
When image read-out is finished as mentioned above, the holding portion 22c of the stimulable phosphor sheet 22 is gripped between the drive rollers 58, 58 and the sheet 22 is supported by rails 23, 23. An erasing section 70 is provided under the stimulable phosphor sheet 22 in this condition. The erasing section 70 is constituted, by way of example, by a surface type erasing light source 71 which faces the sheet 22 from below. The erasing light source 71 is constituted by, for example, an LED panel or an EL (electroluminescence) plate, and mainly emits light having a wavelength within the stimulation wavelength range for the stimulable phosphor constituting the stimulable phoshpor sheet 22. The erasing light source 71 is turned on when image read-out from the sheet 22 is finished. When the sheet 22, specifically the stimulable phosphor layer 22B, is exposed to the erasing light, radiation energy remaining on the sheet 22 after image read-out is released from the sheet 22.
In this manner, the stimulable phosphor sheet 22 on which the image (residual image) has been erased to such an extent that the sheet 22 may be reused for radiation image recording is housed in the case 25. Therefore, it becomes possible to repeat the aforesaid image recording and read-out using the sheet 22. As the erasing light source 71, besides the surface type light source such as the LED panel, it is also possible to use a tungsten-filament lamp, a halogen lamp, an infrared lamp, a xenon flash lamp, a fluorescent lamp or the like as disclosed, for example, in U.S. Patent No. 4,400,619. In the case where such a lamp is used as the erasing light source 71, in order to expose the entire area of the stationary stimulable phosphor sheet 22 in the case 25, a plurality of the lamps may be arrayed side by side, or a rod-like light source may be positioned in the vicinity of the drive rollers 58, 58 therealong for emitting erasing light to the stimulable phosphor sheet 22 conveyed form the case 25 to the light shielding cover 26 before the next radiation image recording is conducted. In the case where residual image erasing is conducted during conveyance of the sheet 22, the substrate 22A of the sheet 22 may be formed of a transparent member, and erasing light may be emitted to the stimulable phosphor layer 22B via the substrate 22A from above the sheet 22.
As shown in Figure 5 showing another embodiment of the radiation image recording and read-out apparatus in accordance with the present invention, when the substrate 22A is formed of a transparent member, the surface type erasing light source 71 may be disposed on the side opposite to the image read-out section 50 with the sheet 22 intervening therebetween. In Figure 5, similar elements are numbered with the same reference numerals with respect to Figures 1 to 4 (this also applies to the other drawings).
As shown in Figure 6 showing a further embodiment of the radiation image recording and read-out apparatus in accordance with the present invention, the erasing light source 71 may be positioned inside of the light shielding cover 26.
For example, in the case where the stimulable phosphor sheet 22 has been maintained for long time in the case 25 without being used for image recording after image (residual image) erasing is conducted on the sheet 22 at the erasing section 70, energy of radiations emitted by radioactive isotopes such as ²²⁶Ra, which are contained in a trace amount in the stimulable phosphor, or energy of environmental radiations may be stored on the sheet 22 and cause noise in a radiation image recorded next on the sheet 22. However, energy of such radiations is also released (secondary erasing) by exposing the sheet 22 to the erasing light emitted by the erasing light source 71 immediately before the image recording. Also in the case where the surface type light source is used as the erasing light source 71, instead of conducting image (residual image) erasing immediately when the stimulable phospohr sheet 22 is returned into the case 25 after the image read-out is finished, the erasing may be carried out just prior to the next radiation image recording. In this case, it is possible to conduct the residual image erasing and the secondary erasing by a single erasing step. Also, in this case, since radiation energy of the residual image component remaining on the stimulable phosphor sheet 22 is naturally released and decays to some extent, it becomes possible to decrease the erasing light amount for the residual image erasing.
In the aforesaid embodiments, image read-out is conducted on the side opposite to the radiation exposure side of the stimulable phosphor sheet 22. However, as shown in Figure 7, the laser beam 52 may be emitted from the radiation exposure side of the sheet 22, and the sheet 22 may be positioned so that the stimulable phosphor layer faces the radiation exposure side, thereby conducting the image read-out from the same side as the radiation exposure side. Also, the stimulable phosphor sheet 22 may be quickly returned into the case 25 after the image recording, and may then be conveyed from the case 25 to the light shielding cover 26, and the image read-out may be conducted during said conveyance. In this case, since the stimulable phosphor sheet 22 before the image read-out is quickly retracted from the position facing the image recording table 32, it is possible to prevent fogging of the sheet 22 caused by environmental radiations or the like.
On the other hand, in order to eliminate various influences caused by variations in radiographic exposure conditions and/or to obtain a radiation image having a high image quality or a high diagnostic efficiency and accuracy, it is necessary to investigate such image input conditions of the radiation image stored on the stimulable phosphor sheet 22 as, for example, the level of radiation dose used for image recording, or the image input pattern which is determined by the portion of the object 34 (e.g. the chest or the abdomen of the human body) or the image recording method used, such as plan image recording or contrasted image recording, before reproducing the radiation image as a visible image, and then to adjust the read-out conditions such as the read-out gain and scale factor and/or the image processing conditions in the read-out circuit 64 based on the detected image input conditions or the image input pattern. The image input conditions and the image input pattern will hereinafter be generically referred to as the image input information. Investigation of the image input information may be conducted prior to the visible image reproduction by use of the method as disclosed in Japanese Unexamined Patent Publication No. 58(1983)-67240. In the disclosed method, a read-out operation for detecting the image input information of the radiation image stored on the stimulable phosphor sheet 22 (hereinafter referred to as the preliminary read-out) is conducted in advance by use of stimulating rays having stimulation energy of a level lower than the level of the stimulation energy of stimulating rays used in a read-out operation for obtaining a visible image for viewing, particularly for diagnostic purposes (hereinafter referred to as the final read-out), and thereafter the final read-out is carried out. In the final read-out, the read-out conditions such as the read-out gain and the scale factor are adjusted to appropriate values, and/or an appropriate image processing is conducted, on the basis of the image input information obtained by the preliminary read-out. Also in the aforesaid embodiments, it is possible to easily conduct the preliminary read-out and the final read-out. Specifically, the preliminary read-out is first conducted while the stimulable phosphor sheet 22 is conveyed from the light shielding cover 26 to the case 25, the sheet 22 is then returned into the light shielding cover 26 (at this time, the erasing light source 71 is not turned on), and thereafter the final read-out is conducted while the sheet 22 is conveyed from the light shielding cover 26 to the case 25. Instead of returning the stimulable phosphor sheet 22 to the light shielding cover 26, the sheet 22 may also be conveyed from the case 25 to the light shielding cover 26 after the preliminary read-out is finished, and the final read-out may be conducted during said conveyance.
Though the erasing light source 71 is positioned inside of the case 25 or the light shielding cover 26 in the aforesaid embodiments, it is also possible to utilize indoor illumination light as the erasing light. Figures 8, 9 and 10 show such embodiments.
In Figure 8, the upper side of the light shielding cover 26 is opened, and a light shielding screen 75 is positioned at the opened side. The light shielding screen 75 is wound up by a wind-up device 76 inside of the case 25 prior to the radiation image recording to lay the stimulable phosphor sheet 22 bare inside of the light shielding cover 26. The bared sheet 22 is subjected to the residual image erasing and/or the secondary erasing by the indoor illumination light. After the erasing is conducted, the light shielding screen 75 is moved to close the upper side of the light shielding cover 26 so that the sheet 22 is not exposed to ambient light.
In another embodiment shown in Figure 9, the upper surface of the light shielding cover 26, i.e. the image recording table 32, is formed of a transparent member, and the light shielding screen 75 is positioned between the image recording table 32 and the stimulable phosphor sheet 22. The light shielding screen 75 is wound up end delivered by the wind-up device 76. In this embodiment, it is possible to place an object on the image recording table 32 unlike the embodiment of Figure 8.
In a further embodiment shown in Figure 10, the upper surface of the image recording table 32 acting as the image recording table 32 is mounted removably. In this embodiment, the stimulable phosphor sheet 22 in the light shielding cover 26 is bared by removing the image recording table 32. The bared sheet 22 may then be subjected to the residual image erasing and/or the secondary erasing by the indoor illumination light. In the case where the indoor illumination light is utilized as the erasing light, though it is possible to effect the erasing with just the indoor light, a long time will be taken for the erasing. Therefore, a small- scale erasing light source should preferably be provided in the apparatus, and the erasing should be conducted with the light emitted by the erasing light source and the indoor light for shortening the erasing time.
The long photomultiplier 59 is described in detail, for example, in Japanese Patent Application No. 60(1985)-156255, and will now be briefly described with reference to Figures 17A, 17B and 18. The long photomultiplier 59 shown in Figures 17A and 17B has an electrode configuration that is generally called a box type. The photomultiplier 59 comprises a vacuum body 151 fabricated of glass or the like,'a photocathode (photoelectric face) 153 positioned to face the long light receiving face 152 for emitting photoelectrons in the vacuum body 151, and a multiplying section 167 positioned under the photocathode 153 in the vacuum body 151 and including a plurality (13 pieces in this example) of electrodes (dynodes) 154 through 166 having a quarter cylinder shape and exhibiting the secondary electron emission effect. A shield electrode 168 is positioned to face the lowermost dynode 166 of the multiplying section 167, and an anode 169 for collecting the electron streams multiplied by the multiplying section 167 and generating a signal positioned inside of the shield electrode 168. These electrodes are respectively connected electrically in a one-to-one relation with terminals 172, 172,... of a terminal group 170 positioned on the side opposite to the light receiving face 152. The dynodes 154 through 166 and the shield electrode 168 are secured inside of the body 151 by supporting members 71, 71, 71 fabricated of an insulating material.
Figure 18 shows an electrical circuit 180 for operating the photomultiplier 59 and obtaining a photoelectric output. In Figure 18, similar elements are numbered with the same reference numerals with respect to Figure 17A. A high negative voltage is applied to the photocathode 153 via a high negative voltage applying terminal 181. The high negative voltage applied to the high negative voltage applying terminal 181 is divided by a bleeder resistance group 182 into voltages which are applied respectively to the dynodes 154 through 166. The shield electrode 168 is grounded, and the anode 169 is grounded via a resistor 183 and is connected with one of the terminals of an amplifier 184. The other terminal of the amplifier 184 is grounded. The photoelectrically converted image information is obtained us an electric signal from an output terminal 185 of the amplifier 184. As the long photomultiplier 59, it is also possible to use a photomultiplier having an electrode configuration generally called a venetian blind type as described, for example, in Japanese Patent Application No. 60(1985)-156255.
The photoelectric read-out means used in the present invention is not limited to the long photomultiplier 59, and it is also possible to a photoelectric read-out means comprising a photodetector having a comparatively small light receiving face, and a light guide member optically coupled with the photodetector as disclosed, for example, in Japanese Unexamined Patent Publication No. 59(1984)-192240. However, the long photomultiplier 59 is advantageous since it solves the problems of increased apparatus size when the large light guide member is used, the decrease in light detection efficiency due to leakage of the light emitted by the stimulable phosphor sheet from the light guide member, and the increased cost of the apparatus because of the fabrication of the light guide member in a complicated shape. Also, when the long photomultiplier 59 is used, it is possibleto improve the light guide efficiency by combining the long photomultiplier 59 wiht the light guide reflection mirror 60, or by combining it with an integrating cylinder as proposed in Japanese Patent Application No. 60(1985)-156257, or by combining an integrating cylinder with a reflection optical element as proposed in Japanese Patent Application No. 60(1985)-156258.
With the aforesaid embodiments, since the stimulable phosphor sheet 22 is conveyed between the case 25 and the light shielding cover 26 in the course of the image read-out, the case 25 may be made small to a size (length and width) slightly larger than the stimulable phosphor sheet 22. However, when the case 25 is made small, the optical path of the laser beam 52 deflected in the case 25 may not be adjusted to be substantially long. In such a case, as shown in Figures 11 and 12, a pair of mirrors 80 and 81 may be positioned between the cylindrical lens 62 and the mirror 57 so that the laser beam 52 is repeatedly reflected between the mirrors 80 and 81 and the optical path is adjusted to be substantially long. Also, as shown in Figure 13, a plurality of mirrors 85, 86, 87, 88 and 89 may be disposed to make the optical path long.
Also, as shown in Figure 14, the radiation image recording and read-out apparatus of the present invention may be fabricated so that the radiation source housing section 30 and the main body 20 are positioned in a horizontally spaced relation to each other and the image recording is conducted with the object 34 in a standing position. Or, as shown in Figure 15, the case 25 may be supported horizontally by a stand 90, the light shielding cover 26 projected out of the case 25 may be positioned under a bed 91, and the image recording may be conducted wiht the object lying on the bed 91. Alternatively, as shown in Figure 16, the case 25 may be supported vertically by the stand 90, and the image recording may be conducted with the object in a standing position.

Claims

1. A radiation image recording and read-out apparatus which comprises:

i) an image recording section (40, 32, 33) for exposing a stimulable phosphor sheet (22; 426) for storing a radiation image thereon which is disposed at an exposure position to a radiation carrying image information to have the radiation image stored on said stimulable phosphor sheet (22; 426),

ii) an image read-out section (50) provided with a transport means (58, 58a, 58b) for moving said stimulable phosphor sheet (22; 426) between said exposure position and a position to which said stimulable phosphor sheet (22; 426) advances and a main scanning means (51-62) for scanning said stimulable phosphor sheet with stimulation rays in a main scanning direction wherein said stimulable phosphor sheet (22; 426) carrying said radiation image stored thereon is exposed to the stimulating rays which cause said stimulable phoshpor sheet (22; 426) to emit light in proportion to the stored radiation energy, and the emitted light is read out by a photoelectric read-out means (64) to obtain an image signal, and

iii) an erasing section (70, 75, 76) for releasing radiation energy energy remaining on said stimulable phosphor sheet (22; 426) for which the image read-out has been conducted at said image read-out section (50), before image recording is conducted on said stimulable phosphor sheet (22; 426)
characterized in that there is provided a case (25; 421) housing said stimulable phosphor sheet (22; 426), and provided with an opening (25a) at one end portion, that there is provided a light shielding cover (26) housed in said case (25, 421) for projection out of said case (25; 421) through said opening (25a), and provided with a sheet passage opening (26a) at an end portion on the side supported by said case (25; 421) at the time of projection out of said case (25; 421), that the exposure position is inside the light shielding cover (26) projected out of the case (25; 421), that the transport means moves the phosphor sheet (22; 426) through said sheet passage opening (26a) into said case (25; 421) and that the main scanning means (51-62) is disposed for scanning the phosphor sheet (22; 426) in the vicinity of said opening of said case inside said case (25; 421).

2. An apparatus as defined in claim 1 wherein said stimulable phosphor sheet (22; 426) comprises a substrate (22A) and a stimulable phosphor layer (22B) overlaid on said substrate (22A) and is positioned so that said stimulable phosphor sheet (22; 426) is exposed to said radiation from the substrate side in said light shielding cover (26), and said stimulable phosphor sheet (22; 426) is exposed to said stimulating rays from the stimulable phosphor layer side at said image read-out section (50).

3. An apparatus as defined in claim 1 wherein said stimulable phosphor sheet (22; 426) comprises a substrate (22A) and a stimulable phosphor layer (22B) overlaid on said substrate (22A) and is positioned so that said stimulable phosphor sheet (22; 426) is exposed to said radiation and said stimulating rays from the stimulable phosphor layer (22B) side at said image read-out section (50).

4. An apparatus as defined in any of claims 1-3 wherein said erasing section comprises an openable light shielding member (75, 32) provided at least on one side of said light shielding cover (26) and opened to expose said stimulable phosphor sheet (22) to external light for erasing.